Wireless interface devices, systems, and methods for use with intravascular pressure monitoring devices

ABSTRACT

Embodiments of the present disclosure are configured to assess the severity of a blockage in a vessel and, in particular, a stenosis in a blood vessel. In some particular embodiments, the devices, systems, and methods of the present disclosure are configured to collect and wirelessly distribute reliable pressure signals to other devices, and do so in a small, compact device that integrates with existing proximal and distal pressure measurement systems and does not require a separate power source.

CROSS-REFERENCE TO RELATED APPLICATIONS

The present application claims priority to and the benefit of U.S.Provisional Patent Application No. 61/745,418, filed Dec. 21, 2012,which is hereby incorporated by reference in its entirety.

TECHNICAL FIELD

The present disclosure relates generally to the assessment of vesselsand, in particular, the assessment of the severity of a blockage orother restriction to the flow of fluid through a vessel. Aspects of thepresent disclosure are particularly suited for evaluation of biologicalvessels in some instances. For example, some particular embodiments ofthe present disclosure are specifically configured for the evaluation ofa stenosis of a human blood vessel.

BACKGROUND

A currently accepted technique for assessing the severity of a stenosisin a blood vessel, including ischemia causing lesions, is fractionalflow reserve (FFR). FFR is a calculation of the ratio of a distalpressure measurement (taken on the distal side of the stenosis) relativeto a proximal pressure measurement (taken on the proximal side of thestenosis). FFR provides an index of stenosis severity that allowsdetermination as to whether the blockage limits blood flow within thevessel to an extent that treatment is required. The normal value of FFRin a healthy vessel is 1.00, while values less than about 0.80 aregenerally deemed significant and require treatment. Common treatmentoptions include angioplasty and stenting.

Coronary blood flow is unique in that it is affected not only byfluctuations in the pressure arising proximally (as in the aorta) but isalso simultaneously affected by fluctuations arising distally in themicrocirculation. Accordingly, it is not possible to accurately assessthe severity of a coronary stenosis by simply measuring the fall in meanor peak pressure across the stenosis because the distal coronarypressure is not purely a residual of the pressure transmitted from theaortic end of the vessel. As a result, for an effective calculation ofFFR within the coronary arteries, it is necessary to reduce the vascularresistance within the vessel. Currently, pharmacological hyperemicagents, such as adenosine, are administered to reduce and stabilize theresistance within the coronary arteries. These potent vasodilator agentsreduce the dramatic fluctuation in resistance (predominantly by reducingthe microcirculation resistance associated with the systolic portion ofthe heart cycle) to obtain a relatively stable and minimal resistancevalue.

However, the administration of hyperemic agents is not always possibleor advisable. First, the clinical effort of administering hyperemicagents can be significant. In some countries (particularly the UnitedStates), hyperemic agents such as adenosine are expensive, and timeconsuming to obtain when delivered intravenously (IV). In that regard,IV-delivered adenosine is generally mixed on a case-by-case basis in thehospital pharmacy. It can take a significant amount of time and effortto get the adenosine prepared and delivered to the operating area. Theselogistic hurdles can impact a physician's decision to use FFR. Second,some patients have contraindications to the use of hyperemic agents suchas asthma, severe COPD, hypotension, bradycardia, low cardiac ejectionfraction, recent myocardial infarction, and/or other factors thatprevent the administration of hyperemic agents. Third, many patientsfind the administration of hyperemic agents to be uncomfortable, whichis only compounded by the fact that the hyperemic agent may need to beapplied multiple times during the course of a procedure to obtain FFRmeasurements. Fourth, the administration of a hyperemic agent may alsorequire central venous access (e.g., a central venous sheath) that mightotherwise be avoided. Finally, not all patients respond as expected tohyperemic agents and, in some instances, it is difficult to identifythese patients before administration of the hyperemic agent.

To obtain FFR measurements or other similar measurements such as aninstantaneous wave-free ratio (iFR) measurement, one or moreultra-miniature sensors placed on the distal portion of a flexibledevice, such as a catheter or guide wire used for catheterizationprocedures, are utilized to obtain the distal pressure measurement,while a sensor connected to a measurement instrument, often called thehemodynamic system, is utilized to obtain the proximal or aorticpressure measurement. Currently only large expensive systems or acombination of multiple devices connected to the distal pressure wireand the hemodynamic system can calculate and display an FFR measurement.In that regard, to calculate the FFR or iFR these devices require boththe aortic or proximal pressure measurement and the coronary artery ordistal pressure measurement. Accordingly, these systems require thecatheter lab's hemodynamic system to have a high level analog voltageoutput. “High level” in this context generally implies 100 mmHg/Voltoutput. Unfortunately, there are many hemodynamic systems that don'tprovide a high level output. As a result, when using these hemodynamicsystems, providing an FFR measurement or other measurement that requiresan aortic pressure measurement is difficult if not impossible. Further,space in a typical catheter lab is extremely limited. Consequently,devices that are large and located in the catheter lab are disfavoredcompared to smaller devices, especially if the smaller device canprovide much if not all of the functionality of the larger device. As aresult, it is highly desirable to have a device that that can collectboth distal and aortic pressure measurements and yet is small andlightweight that can sit on, or near, the patient bed and be easily readby the physician.

Further, most pressure measurement devices require an extra source ofpower like an AC adapter or wall plug. This adds to wire clutter andavailable medical grade AC outlets are not often available near thepatient bed. In addition, any device that uses AC power must undergostringent safety precautions to reduce patient risk due to leakagecurrents. Batteries are another alternative for power. But, batteriesmust be replaced, disposed of correctly and have a finite shelf life.

Additionally, many pressure measurement devices transmit receivedpressure data to one or more other devices via wires that must be routedand accounted for within a catheter lab. These wires add to the wireclutter and therefore increase the risk of accidents. Further, computingsystems inside or outside of a catheter lab frequently rely on pressuremeasurements for the calculation of pressure-based diagnosticcharacterizations, such as FFR or iFR. For reliable diagnosticcharacterizations, a strong aortic pressure signal is often needed.Current hemodynamic systems sometimes fail to provide a strong andreliable aortic pressure signal, which may lead to an inaccurate orincomplete patient diagnosis.

Accordingly, there remains a need for improved devices, systems, andmethods for assessing the severity of a blockage in a vessel and, inparticular, a stenosis in a blood vessel. In that regard, there remainsa need for improved devices, systems, and methods for collecting anddistributing reliable pressure signals that have a small, compact size(e.g., suitable for hand-held use), integrate with existing proximal anddistal pressure measurement devices, and do not require a separate powersource.

SUMMARY

Embodiments of the present disclosure are configured to assess theseverity of a blockage in a vessel and, in particular, a stenosis in ablood vessel. In some particular embodiments, the devices, systems, andmethods of the present disclosure are configured to collect andwirelessly distribute reliable pressure signals to other devices, and doso in a small, compact device that integrates with existing proximal anddistal pressure measurement systems and does not require a separatepower source.

In one embodiment, an interface for intravascular pressure sensingdevices is provided. The interface comprises: a distal input configuredto receive a distal pressure signal from a distal pressure sensingdevice; a distal output configured to output the distal pressure signalto a hemodynamic system in a format useable by the hemodynamic system; aproximal input configured to receive a proximal pressure signal from aproximal pressure sensing device; a proximal output configured to outputthe proximal pressure signal to the hemodynamic system in a formatuseable by the hemodynamic system; and a wireless transceiver coupled tothe distal input, distal output, proximal input, and proximal output,the wireless transceiver being configured to wirelessly transmit thedistal pressure and the proximal pressure to a computing system spacedfrom the interface, wherein the computing system is distinct from thehemodynamic system. In some embodiments, the distal input, distaloutput, proximal input, proximal output, and wireless transceiver aresecured to a housing. Further, in some instances the distal pressuresensing device is a pressure-sensing guidewire and the proximal pressuresensing device is a pressure-sensing catheter configured for use withthe hemodynamic system.

In another embodiment, a system for evaluating a vascular stenosis isprovided. The system comprises: a distal pressure sensing device sizedand shaped for insertion into human vasculature; a proximal pressuresensing device sized and shaped for insertion into human vasculature;and an interface, where the interface includes: a distal inputconfigured to receive a distal pressure signal from the distal pressuresensing device; a proximal input configured to receive a proximalpressure signal from the proximal pressure sensing device; a proximaloutput configured to output the proximal pressure signal to a processingsystem in a format useable by the processing system; and a wirelesstransceiver coupled to the distal input, distal output, proximal input,and proximal output, the wireless transceiver being configured towirelessly transmit the distal pressure and the proximal pressure to acomputing system spaced from the interface, wherein the computing systemis distinct from the processing system. In some instances, theprocessing system is a hemodynamic system. Further, in some instancesthe distal input, distal output, proximal input, proximal output, andwireless transceiver are secured to a housing. In some instances, thedistal pressure sensing device is a pressure-sensing guidewire and theproximal pressure sensing device is a pressure-sensing catheterconfigured for use with the processing system.

Additional aspects, features, and advantages of the present disclosurewill become apparent from the following detailed description.

BRIEF DESCRIPTION OF THE DRAWINGS

Illustrative embodiments of the present disclosure will be describedwith reference to the accompanying drawings, of which:

FIG. 1 is a diagrammatic perspective view of a vessel having a stenosisaccording to an embodiment of the present disclosure.

FIG. 2 is a diagrammatic, partial cross-sectional perspective view of aportion of the vessel of FIG. 1 taken along section line 2-2 of FIG. 1.

FIG. 3 is a diagrammatic, partial cross-sectional perspective view ofthe vessel of FIGS. 1 and 2 with instruments positioned thereinaccording to an embodiment of the present disclosure.

FIG. 4 is a diagrammatic, schematic view of a system according to anembodiment of the present disclosure.

FIG. 5 is a diagrammatic, schematic view of an interface device of thesystem of FIG. 4 according to an embodiment of the present disclosure.

FIG. 6 is a diagrammatic, schematic view of a portion of the interfacedevice of FIG. 5 according to an embodiment of the present disclosure.

FIG. 7 is a diagrammatic, schematic view of a portion of the interfacedevice of FIG. 5 similar to that of FIG. 6, but illustrating anotherembodiment of the present disclosure.

DETAILED DESCRIPTION

For the purposes of promoting an understanding of the principles of thepresent disclosure, reference will now be made to the embodimentsillustrated in the drawings, and specific language will be used todescribe the same. It is nevertheless understood that no limitation tothe scope of the disclosure is intended. Any alterations and furthermodifications to the described devices, systems, and methods, and anyfurther application of the principles of the present disclosure arefully contemplated and included within the present disclosure as wouldnormally occur to one skilled in the art to which the disclosurerelates. In particular, it is fully contemplated that the features,components, and/or steps described with respect to one embodiment may becombined with the features, components, and/or steps described withrespect to other embodiments of the present disclosure. For the sake ofbrevity, however, the numerous iterations of these combinations will notbe described separately.

Referring to FIGS. 1 and 2, shown therein is a vessel 100 having astenosis according to an embodiment of the present disclosure. In thatregard, FIG. 1 is a diagrammatic perspective view of the vessel 100,while FIG. 2 is a partial cross-sectional perspective view of a portionof the vessel 100 taken along section line 2-2 of FIG. 1. Referring morespecifically to FIG. 1, the vessel 100 includes a proximal portion 102and a distal portion 104. A lumen 106 extends along the length of thevessel 100 between the proximal portion 102 and the distal portion 104.In that regard, the lumen 106 is configured to allow the flow of fluidthrough the vessel. In some instances, the vessel 100 is a blood vessel.In some particular instances, the vessel 100 is a coronary artery. Insuch instances, the lumen 106 is configured to facilitate the flow ofblood through the vessel 100.

As shown, the vessel 100 includes a stenosis 108 between the proximalportion 102 and the distal portion 104. Stenosis 108 is generallyrepresentative of any blockage or other structural arrangement thatresults in a restriction to the flow of fluid through the lumen 106 ofthe vessel 100. Embodiments of the present disclosure are suitable foruse in a wide variety of vascular applications, including withoutlimitation coronary, peripheral (including but not limited to lowerlimb, carotid, and neurovascular), renal, and/or venous. Where thevessel 100 is a blood vessel, the stenosis 108 may be a result of plaquebuildup, including without limitation plaque components such as fibrous,fibro-lipidic (fibro fatty), necrotic core, calcified (dense calcium),blood, fresh thrombus, and mature thrombus. Generally, the compositionof the stenosis will depend on the type of vessel being evaluated. Inthat regard, it is understood that the concepts of the presentdisclosure are applicable to virtually any type of blockage or othernarrowing of a vessel that results in decreased fluid flow.

Referring more particularly to FIG. 2, the lumen 106 of the vessel 100has a diameter 110 proximal of the stenosis 108 and a diameter 112distal of the stenosis. In some instances, the diameters 110 and 112 aresubstantially equal to one another. In that regard, the diameters 110and 112 are intended to represent healthy portions, or at leasthealthier portions, of the lumen 106 in comparison to stenosis 108.Accordingly, these healthier portions of the lumen 106 are illustratedas having a substantially constant cylindrical profile and, as a result,the height or width of the lumen has been referred to as a diameter.However, it is understood that in many instances these portions of thelumen 106 will also have plaque buildup, a non-symmetric profile, and/orother irregularities, but to a lesser extent than stenosis 108 and,therefore, will not have a cylindrical profile. In such instances, thediameters 110 and 112 are understood to be representative of a relativesize or cross-sectional area of the lumen and do not imply a circularcross-sectional profile.

As shown in FIG. 2, stenosis 108 includes plaque buildup 114 thatnarrows the lumen 106 of the vessel 100. In some instances, the plaquebuildup 114 does not have a uniform or symmetrical profile, makingangiographic evaluation of such a stenosis unreliable. In theillustrated embodiment, the plaque buildup 114 includes an upper portion116 and an opposing lower portion 118. In that regard, the lower portion118 has an increased thickness relative to the upper portion 116 thatresults in a non-symmetrical and non-uniform profile relative to theportions of the lumen proximal and distal of the stenosis 108. As shown,the plaque buildup 114 decreases the available space for fluid to flowthrough the lumen 106. In particular, the cross-sectional area of thelumen 106 is decreased by the plaque buildup 114. At the narrowest pointbetween the upper and lower portions 116, 118 the lumen 106 has a height120, which is representative of a reduced size or cross-sectional arearelative to the diameters 110 and 112 proximal and distal of thestenosis 108. Note that the stenosis 108, including plaque buildup 114is exemplary in nature and should be considered limiting in any way. Inthat regard, it is understood that the stenosis 108 has other shapesand/or compositions that limit the flow of fluid through the lumen 106in other instances. While the vessel 100 is illustrated in FIGS. 1 and 2as having a single stenosis 108 and the description of the embodimentsbelow is primarily made in the context of a single stenosis, it isnevertheless understood that the devices, systems, and methods describedherein have similar application for a vessel having multiple stenosisregions.

Referring now to FIG. 3, the vessel 100 is shown with instruments 130and 132 positioned therein according to an embodiment of the presentdisclosure. In general, instruments 130 and 132 may be any form ofdevice, instrument, or probe sized and shaped to be positioned within avessel. In the illustrated embodiment, instrument 130 is generallyrepresentative of a guide wire, while instrument 132 is generallyrepresentative of a catheter. In that regard, instrument 130 extendsthrough a central lumen of instrument 132. However, in otherembodiments, the instruments 130 and 132 take other forms. In thatregard, the instruments 130 and 132 are of similar form in someembodiments. For example, in some instances, both instruments 130 and132 are guide wires. In other instances, both instruments 130 and 132are catheters. On the other hand, the instruments 130 and 132 are ofdifferent form in some embodiments, such as the illustrated embodiment,where one of the instruments is a catheter and the other is a guidewire. Further, in some instances, the instruments 130 and 132 aredisposed coaxial with one another, as shown in the illustratedembodiment of FIG. 3. In other instances, one of the instruments extendsthrough an off-center lumen of the other instrument. In yet otherinstances, the instruments 130 and 132 extend side-by-side. In someparticular embodiments, at least one of the instruments is as arapid-exchange device, such as a rapid-exchange catheter. In suchembodiments, the other instrument is a buddy wire or other deviceconfigured to facilitate the introduction and removal of therapid-exchange device. Further still, in other instances, instead of twoseparate instruments 130 and 132 a single instrument is utilized. Inthat regard, the single instrument incorporates aspects of thefunctionalities (e.g., data acquisition) of both instruments 130 and 132in some embodiments.

Instrument 130 is configured to obtain diagnostic information about thevessel 100. In that regard, the instrument 130 includes one or moresensors, transducers, and/or other monitoring elements configured toobtain the diagnostic information about the vessel. The diagnosticinformation includes one or more of pressure, flow (velocity), images(including images obtained using ultrasound (e.g., IVUS), OCT, thermal,and/or other imaging techniques), temperature, and/or combinationsthereof. The one or more sensors, transducers, and/or other monitoringelements are positioned adjacent a distal portion of the instrument 130in some instances. In that regard, the one or more sensors, transducers,and/or other monitoring elements are positioned less than 30 cm, lessthan 10 cm, less than 5 cm, less than 3 cm, less than 2 cm, and/or lessthan 1 cm from a distal tip 134 of the instrument 130 in some instances.In some instances, at least one of the one or more sensors, transducers,and/or other monitoring elements is positioned at the distal tip of theinstrument 130.

The instrument 130 includes at least one element configured to monitorpressure within the vessel 100. The pressure monitoring element can takethe form a piezo-resistive pressure sensor, a piezo-electric pressuresensor, a capacitive pressure sensor, an electromagnetic pressuresensor, a fluid column (the fluid column being in communication with afluid column sensor that is separate from the instrument and/orpositioned at a portion of the instrument proximal of the fluid column),an optical pressure sensor, and/or combinations thereof. In someinstances, one or more features of the pressure monitoring element areimplemented as a solid-state component manufactured using semiconductorand/or other suitable manufacturing techniques. Examples of commerciallyavailable guide wire products that include suitable pressure monitoringelements include, without limitation, the PrimeWire PRESTIGE® PLUSpressure guide wire, the PrimeWire PRESTIGE® pressure guide wire, thePrimeWire® pressure guide wire, and the ComboWire® XT pressure and flowguide wire, each available from Volcano Corporation, as well as thePressureWire™ Certus guide wire and the PressureWire™ Aeris guide wire,each available from St. Jude Medical, Inc. Generally, the instrument 130is sized such that it can be positioned through the stenosis 108 withoutsignificantly impacting fluid flow across the stenosis, which wouldimpact the distal pressure reading. Accordingly, in some instances theinstrument 130 has an outer diameter of 0.018″ or less. In someembodiments, the instrument 130 has an outer diameter of 0.014″ or less.

Instrument 132 is also configured to obtain diagnostic information aboutthe vessel 100. In some instances, instrument 132 is configured toobtain the same diagnostic information as instrument 130. In otherinstances, instrument 132 is configured to obtain different diagnosticinformation than instrument 130, which may include additional diagnosticinformation, less diagnostic information, and/or alternative diagnosticinformation. The diagnostic information obtained by instrument 132includes one or more of pressure, flow (velocity), images (includingimages obtained using ultrasound (e.g., IVUS), OCT, thermal, and/orother imaging techniques), temperature, and/or combinations thereof.Instrument 132 includes one or more sensors, transducers, and/or othermonitoring elements configured to obtain this diagnostic information. Inthat regard, the one or more sensors, transducers, and/or othermonitoring elements are positioned adjacent a distal portion of theinstrument 132 in some instances. In that regard, the one or moresensors, transducers, and/or other monitoring elements are positionedless than 30 cm, less than 10 cm, less than 5 cm, less than 3 cm, lessthan 2 cm, and/or less than 1 cm from a distal tip 136 of the instrument132 in some instances. In some instances, at least one of the one ormore sensors, transducers, and/or other monitoring elements ispositioned at the distal tip of the instrument 132.

Similar to instrument 130, instrument 132 also includes at least oneelement configured to monitor pressure within the vessel 100. Thepressure monitoring element can take the form a piezo-resistive pressuresensor, a piezo-electric pressure sensor, a capacitive pressure sensor,an electromagnetic pressure sensor, a fluid column (the fluid columnbeing in communication with a fluid column sensor that is separate fromthe instrument and/or positioned at a portion of the instrument proximalof the fluid column), an optical pressure sensor, and/or combinationsthereof. In some instances, one or more features of the pressuremonitoring element are implemented as a solid-state componentmanufactured using semiconductor and/or other suitable manufacturingtechniques. Currently available catheter products suitable for use withone or more of Siemens AXIOM Sensis, Mennen Horizon XVu, and PhilipsXper IM Physiomonitoring 5 and that include pressure monitoring elementscan be utilized for instrument 132 in some instances.

In accordance with aspects of the present disclosure, at least one ofthe instruments 130 and 132 is configured to monitor a pressure withinthe vessel 100 distal of the stenosis 108 and at least one of theinstruments 130 and 132 is configured to monitor a pressure within thevessel proximal of the stenosis. In that regard, the instruments 130,132 are sized and shaped to allow positioning of the at least oneelement configured to monitor pressure within the vessel 100 to bepositioned proximal and/or distal of the stenosis 108 as necessary basedon the configuration of the devices. In that regard, FIG. 3 illustratesa position 138 suitable for measuring pressure distal of the stenosis108. The position 138 is less than 5 cm, less than 3 cm, less than 2 cm,less than 1 cm, less than 5 mm, and/or less than 2.5 mm from the distalend of the stenosis 108 (as shown in FIG. 2) in some instances. FIG. 3also illustrates a plurality of suitable positions for measuringpressure proximal of the stenosis 108. In that regard, positions 140,142, 144, 146, and 148 each represent a position that is suitable formonitoring the pressure proximal of the stenosis in some instances. Inthat regard, the positions 140, 142, 144, 146, and 148 are positioned atvarying distances from the proximal end of the stenosis 108 ranging frommore than 20 cm down to about 5 mm or less. Generally, the proximalpressure measurement will be spaced from the proximal end of thestenosis. Accordingly, in some instances, the proximal pressuremeasurement is taken at a distance equal to or greater than an innerdiameter of the lumen of the vessel from the proximal end of thestenosis. In the context of coronary artery pressure measurements, theproximal pressure measurement is generally taken at a position proximalof the stenosis and distal of the aorta, within a proximal portion ofthe vessel. However, in some particular instances of coronary arterypressure measurements, the proximal pressure measurement is taken from alocation inside the aorta. In other instances, the proximal pressuremeasurement is taken at the root or ostium of the coronary artery. Insome instances, the proximal pressure measurement is referred to as theaortic pressure.

Referring now to FIG. 4, shown therein is a system 150 according to anembodiment of the present disclosure. In that regard, FIG. 4 is adiagrammatic, schematic view of the system 150. As shown, the system 150includes an instrument 152. In that regard, in some instances instrument152 is suitable for use as at least one of instruments 130 and 132discussed above. Accordingly, in some instances the instrument 152includes features similar to those discussed above with respect toinstruments 130 and 132 in some instances. In the illustratedembodiment, the instrument 152 is a guide wire having a distal portion154 and a housing 156 positioned adjacent the distal portion. In thatregard, the housing 156 is spaced approximately 3 cm from a distal tipof the instrument 152. The housing 156 is configured to house one ormore sensors, transducers, and/or other monitoring elements configuredto obtain the diagnostic information about the vessel. In theillustrated embodiment, the housing 156 contains at least a pressuresensor configured to monitor a pressure within a lumen in which theinstrument 152 is positioned. A shaft 158 extends proximally from thehousing 156. A torque device 160 is positioned over and coupled to aproximal portion of the shaft 158. A proximal end portion 162 of theinstrument 152 is coupled to a connector 164. A cable 166 extends fromconnector 164 to a connector 168. In some instances, connector 168 isconfigured to be plugged into an interface 170. In that regard,interface 170 is a patient interface module (PIM) in some instances, butin other instances it may be a hub that routes data signals to varioussystems and devices. In some instances, the cable 166 is replaced with awireless connection. In that regard, the interface 170 includes anantenna 171 for wireless data transmissions. It is understood thatvarious communication pathways between the instrument 152 and theinterface 170 may be utilized, including physical connections (includingelectrical, optical, and/or fluid connections), wireless connections,and/or combinations thereof.

The interface 170 is communicatively coupled to a hemodynamic system 172via a connection 174. In some instances, the hemodynamic system 172 is aSiemens AXIOM Sensis, a Mennen Horizon XVu, or a Philips Xper IMPhysiomonitoring 5. Together, connector 164, cable 166, connector 168,interface 170, and connection 174 facilitate communication between theone or more sensors, transducers, and/or other monitoring elements ofthe instrument 152 and the hemodynamic system 172. However, thiscommunication pathway is exemplary in nature and should not beconsidered limiting in any way. In that regard, it is understood thatany communication pathway between the instrument 152 and the interface170 may be utilized, including physical connections (includingelectrical, optical, and/or fluid connections), wireless connections,and/or combinations thereof. In that regard, the hemodynamic system 172includes an antenna 173 for wireless data transmissions. Similarly, itis understood that any communication pathway between the interface 170and the hemodynamic system 172 may be utilized, including physicalconnections (including electrical, optical, and/or fluid connections),wireless connections, and/or combinations thereof. Accordingly, it isunderstood that additional components (e.g., connectors, routers,switches, etc.) not illustrated in FIG. 4 may be included to facilitatecommunication between the instrument 152, the interface 170, and thehemodynamic system 172.

In some embodiments, the connection 174 is a wireless connection. Insome instances, the connection 174 includes a communication link over anetwork (e.g., intranet, internet, telecommunications network, and/orother network). In that regard, it is understood that the hemodynamicsystem 172 is positioned remote from an operating area where theinstrument 152 is being used in some instances. Having the connection174 include a connection over a network can facilitate communicationbetween the instrument 152 and the remote hemodynamic system 172regardless of whether the hemodynamic system is in an adjacent room, anadjacent building, or in a different state/country. Further, it isunderstood that the communication pathway between the instrument 152 andthe hemodynamic system 172 is a secure connection in some instances.Further still, it is understood that, in some instances, the datacommunicated over one or more portions of the communication pathwaybetween the instrument 152 and the hemodynamic system 172 is encrypted.

The system 150 also includes an instrument 175. In that regard, in someinstances instrument 175 is suitable for use as at least one ofinstruments 130 and 132 discussed above. Accordingly, in some instancesthe instrument 175 includes features similar to those discussed abovewith respect to instruments 130 and 132. In the illustrated embodiment,the instrument 175 is a catheter-type device. In that regard, theinstrument 175 includes one or more sensors, transducers, and/or othermonitoring elements adjacent a distal portion of the instrumentconfigured to obtain the diagnostic information about the vessel. In theillustrated embodiment, the instrument 175 includes a pressure sensorconfigured to monitor a pressure within a lumen in which the instrument175 is positioned. In one particular embodiment, instrument 175 is apressure-sensing catheter that includes a fluid column extending alongits length. In such an embodiment, a hemostasis valve is fluidly coupledto the fluid column of the catheter, a manifold is fluidly coupled tothe hemostasis valve, and tubing extends between the components asnecessary to fluidly couple the components. In that regard, the fluidcolumn of the catheter is in fluid communication with a pressure sensorvia the valve, manifold, and tubing. In some instances, the pressuresensor is part of or in communication with hemodynamic system 172. Inother instances, the pressure sensor is a separate component positionedbetween the instrument 175 and the interface 170 or between theinterface 170 and the hemodynamic system 172. The instrument 175 is incommunication with the interface 170 via connection 177. The interface170, in turn, is communicatively coupled to the computing device 172 viaa connection 178.

Similar to the connections between instrument 152 and the interface 170and the hemodynamic system 172, connections 177 and 178 facilitatecommunication between the one or more sensors, transducers, and/or othermonitoring elements of the instrument 175 and the interface 170 and thehemodynamic system 172. Again, however, this communication pathway isexemplary in nature and should not be considered limiting in any way. Inthat regard, it is understood that any communication pathway between theinstrument 175 and the interface 170 may be utilized, including physicalconnections (including electrical, optical, and/or fluid connections),wireless connections, and/or combinations thereof. Similarly, it isunderstood that any communication pathway between the interface 170 andthe hemodynamic system 172 may be utilized, including physicalconnections (including electrical, optical, and/or fluid connections),wireless connections, and/or combinations thereof. Accordingly, it isunderstood that additional components (e.g., connectors, routers,switches, etc.) not illustrated in FIG. 4 may be included to facilitatecommunication between the instrument 175, the interface 170, and thehemodynamic system 172.

In some embodiments, the connection 178 is a wireless connection. Insome instances, the connection 178 includes a communication link over anetwork (e.g., intranet, internet, telecommunications network, and/orother network). In that regard, it is understood that the hemodynamicsystem 172 is positioned remote from an operating area where theinstrument 175 is being used in some instances. Having the connection178 include a connection over a network can facilitate communicationbetween the instrument 175 and the remote hemodynamic system 172regardless of whether the computing device is in an adjacent room, anadjacent building, or in a different state/country. Further, it isunderstood that the communication pathway between the instrument 175 andthe hemodynamic system 172 is a secure connection in some instances.Further still, it is understood that, in some instances, the datacommunicated over one or more portions of the communication pathwaybetween the instrument 175 and the hemodynamic system 172 is encrypted.

It is understood that one or more components of the system 150 are notincluded, are implemented in a different arrangement/order, and/or arereplaced with an alternative device/mechanism in other embodiments ofthe present disclosure. Alternatively, additional components and/ordevices may be implemented into the system. Generally speaking, thecommunication pathway between either or both of the instruments 152, 175and the hemodynamic system 172 may have no intermediate nodes (i.e., adirect connection), one intermediate node between the instrument and thecomputing device, or a plurality of intermediate nodes between theinstrument and the computing device.

In some embodiments, the interface 170 includes a wireless transceiverand is configured to wirelessly transmit pressure readings from one orboth of the instruments 152 and 175 to other devices in the system 150,such as a computing device 180. For example, the interface 170 maywirelessly transmit a distal pressure and/or distal pressure waveform, aproximal (i.e., aortic) pressure and/or proximal pressure waveform, tothe computing device 180. In one embodiment, the computing device 180 isa computer system with the hardware and software to acquire, process,and display multi-modality medical data, but, in other embodiments, thecomputing device 180 may be any other type of computing system operableto process medical data. For example, in some instances the computingdevice 180 utilizes the distal pressure and/or distal pressure waveformwith the proximal pressure and/or proximal pressure waveform tocalculate FFR, calculate iFR, calculate a pressure differential betweenthe proximal and distal pressures, identify a suitable diagnostic windowfor performing a pressure differential calculation without administeringa hyperemic agent to the patient, calculate a pressure differentialduring the identified diagnostic window, calculate any other medicaldiagnostic characterization that is influenced by distal pressure and/orproximal (i.e., aortic) pressure, and any combinations thereof.

In the embodiments in which computing device 180 is a computerworkstation, the system includes at least a processor such as amicrocontroller or a dedicated central processing unit (CPU), anon-transitory computer-readable storage medium such as a hard drive,random access memory (RAM), and/or optical read only memory (CD-ROM,DVD-ROM, Blu-Ray), a video controller such as a graphics processing unit(GPU), and a network communication device such as an Ethernet controlleror a wireless communication transceiver 182. In some instances, thecomputing device 180 is portable (e.g., handheld, on a rolling cart,etc.). Further, it is understood that in some instances computing device180 comprises a plurality of computing devices. In some instances, themedical system 150 is deployed in a catheter lab having a control room,with the computing device 180 being located in the control room or thecatheter lab itself. In other embodiments, the computing device 180 maybe located elsewhere, such as in a centralized information technologyarea in a medical facility, or at an off-site location (i.e., in thecloud).

In some embodiments, the interface 170 itself includes a processor andrandom access memory and is programmed to execute steps associated withthe data acquisition and analysis described herein. In particular, insome embodiments the interface 170 is configured to receive and displaypressure readings from one or both of the instruments 152 and 175 and/orcalculate (and display) FFR or other pressure differential based on thepressure measurements obtained from the instruments 152 and 175.Accordingly, it is understood that any steps related to dataacquisition, data processing, instrument control, and/or otherprocessing or control aspects of the present disclosure, including thoseincorporated by reference, may be implemented by the interface 170 usingcorresponding instructions stored on or in a non-transitory computerreadable medium accessible by the computing device. In some embodiments,the interface 170 includes one or more processing and/or signalconditioning features and/or associated components/circuitry asdescribed in U.S. Pat. No. 6,585,660, which is hereby incorporated byreference in its entirety.

In the embodiments in which the interface 170 includes a wirelesstransceiver and is also configured to calculate FFR, iFR, or anotherdiagnostic characterization differential based on the pressuremeasurements obtained from the instruments 152 and 175, the interface170 may first calculate the diagnostic characterization and thenwirelessly transmit the pre-calculated result to one or more otherdevices such as the computing device 180 and/or hemodynamic system 172.

In the illustrated embodiment of FIG. 4, the interface 170 includes ahousing 184. The housing 184 contains the electronic components of theinterface 170. In that regard, exemplary embodiments of electroniccomponent arrangements suitable for interface 170 as described belowwith respect to FIGS. 5 and 6. In some embodiments, the interface 170 issized to be handheld and/or sized to be positioned on or near a patientbed (e.g., attached to a bed rail or IV pole). In that regard, in someinstances the interface 170 is similar in size to the SmartMap® PressureInstrument available from Volcano Corporation, which has housingdimensions of approximately 15.75 cm (6.3″) wide, 8.853 cm (3.54″) tall,and 4.48 cm (1.79″) deep. Generally, the interface 170 has a widthbetween about 5 cm and about 25 cm, a height between about 5 cm andabout 25 cm, and a depth between about 1 cm and about 10 cm. In someinstances, the interface 170 also includes a display and one or morevirtual or physical buttons configured to facilitate use of theinterface.

Referring now to FIG. 5, shown therein is a schematic of the interface170 according to an exemplary embodiment of the present disclosure. Inthat regard, the interface 170 includes an input connector 190 forreceiving signals from a distal pressure sensing component 191.Accordingly, in some embodiments with an arrangement similar to thatshown in FIG. 4, input connector 190 is configured to receive theconnector 168 that is in communication with instrument 152, where distalpressure sensing component 191 is a pressure sensing component of theinstrument 152. The interface 170 also includes an output connector 192configured to send a distal pressure signal to a distal pressure input193 of a hemo system or other computing device. Accordingly, in someembodiments with an arrangement similar to that shown in FIG. 4, outputconnector 192 is configured to send the distal pressure signal to aninput of the hemodynamic system 172 over connection 174. In that regard,in some embodiments the distal pressure signal is modulated based on thehemo system's excitation voltage to provide a low level output of thedistal pressure signal to the hemo system. A low level output in thiscontext is typically 5 μV/Vexc/mmHg, where Vexc is the excitationvoltage. However, larger or smaller level outputs are used in someinstances.

The interface 170 further includes a wireless transceiver 206 that isconfigured to wireless transmit medical data provided to the interface170. The wireless transceiver 206 may be any type of wirelesscommunications module capable of wirelessly transmitting data to otherdevices spaced from the interface 170. For instance, the wirelesstransceiver 206 may transmit data using IEEE 802.11 Wi-Fi standards,Bluetooth standards, cellular standards (i.e., GSM, CDMA, HSDPA, LTE,etc), Ultra Wide-Band (UWB) standards, wireless FireWire standards,wireless USB standards, and/or any other short-range, medium-range,and/or long-range wireless standards. In the illustrated embodiment ofFIG. 5, the wireless transceiver 206 receives a distal pressure signalfrom the input connector 190 and subsequently passes the distal pressuresignal to the output connector 192. Upon receiving the distal pressuresignal, the wireless transceiver 206 may wirelessly transmit the distalpressure signal to one or more remote devices such as a computing systemconfigured to calculate FFR, iFR, or another pressure-based diagnosticcharacterization. The wireless transceiver 206 may transmit the distalpressure signal by itself or it may combine the distal pressure signalwith other received medical data such as a proximal pressure signal andtransmit the signals together. In one instance, the distal pressuresignal is converted from an analog signal to a digital signal with anAnalog-to-Digital converter (ADC) prior to reaching the wirelesstransceiver 206. In other instance, the wireless transceiver 206performs the analog-to-digital itself prior to transmitting the distalpressure signal.

In a medical facility with a plurality of devices wirelesslytransmitting medical data, such medical data must be tightly correlatedwith the patient from whom the medical data was acquired. In thatregard, in some embodiments, the wireless transceiver 206 may associatethe medical data with identification information (e.g., a uniqueidentifier, patient name, patient social security number, patient dateof birth, procedure location, procedure time, practitioner name, etc.)before wirelessly transmitting the medical data to one or more remotedevices. For instance, the wireless transceiver 206 may convert receivedmedical data into a plurality of messages (i.e., packets) containingboth the medical data and associated identifying information, and thenwirelessly transmit the plurality of messages. Additional details ofmessage formats that associate medical data with identifying patientinformation are described in U.S. Provisional Patent Application No.61/473,591, filed on Aug. 8, 2011 and titled “DISTRIBUTED MEDICALSENSING SYSTEM AND METHOD,” which is hereby incorporated by reference inits entirety. Further, in some instances, the wireless transceiver 206is configured to wirelessly transmit any pressure data over a securecommunication link. For instance, the wireless transceiver 206 maytransmit over a wireless network secured with Wired Equivalent Privacy(WEP), Wi-Fi Protected Access (WPA), Extensible Authentication Protocol(EAP), or another type of wireless security. Further, the wirelesstransceiver 206 may encrypt and/or compress any data prior totransmission.

In some embodiments, the output connector 192 is also used to facilitateenergy harvesting from the hemo system or other pressure measuringsystem. In that regard, to eliminate the need for an additional powersupply within the interface 170, a power extraction circuit 220 extractsa small amount of power from the hemo system's excitation voltageassociated with the distal pressure input 193. The power extractioncircuit 220 converts the extracted energy into the power needed to runthe remaining circuitry of the interface 170. In some instances, thepower extraction circuit 220 is configured to be the only power sourceused to power the components of interface 170. Since the excitationsignal can be AC, positive or negative DC, and/or have various wave formshapes and voltages, the power extraction circuit 220 must be able toaccept these and convert to a regulated power supply. In that regard,the voltage extracted from the excitation signal is converted to aregulated Vcc voltage to operate the low power circuitry using a buck orboost regulator depending on the input voltage. A current limiterminimizes distortion to the hemo system's waveform at the peaks. In someinstances, the current is limited to a level below the AAMI transducerlimits as to be compatible with most hemo systems. In some instances,the hemo system's excitation voltage meets the IEC 60601-2-34 standard.In some alternative embodiments, the power extraction circuit 220 isconfigured to interface with a battery or other rechargeable powersupply device that can be utilized to power the components of theinterface. In some alternative embodiments, the power extraction circuit220 is configured to interface with an AC adapter that is to be pluggedinto a wall outlet in order to provide power to the components of theinterface.

The interface 170 also includes input/output connectors 194 and 195 forinterfacing with a proximal pressure measurement system. In someparticular embodiments, the input/output connectors 194 and 195 areconfigured to work with a pressure monitoring device of a hemo system.Generally, the input/output connector 194 is configured to receivesignals from a proximal pressure sensing component 196. In someinstances, the proximal pressure sensing component 196 is a transducerconfigured to detect aortic pressure. Accordingly, in some embodimentswith an arrangement similar to that shown in FIG. 4, input/outputconnector 194 is configured to receive signals from instrument 175,where the proximal pressure sensing component 196 is a pressure sensingcomponent associated with the instrument 175. The input/output connector195 is configured to send a proximal pressure signal to a proximalpressure input 197 of a hemo system or other computing device.Accordingly, in some embodiments with an arrangement similar to thatshown in FIG. 4, the input/output connector 195 is configured to sendthe proximal pressure signal to an input of hemodynamic system 172 overconnection 178.

In the illustrated embodiment of FIG. 5, conductors 200 and 202 carry anexcitation signal to the proximal pressure sensing component 196. Anamplifier 204 is electrically connected to the conductors 200 and 202 asshown. The amplifier 204 is an operational amplifier in someembodiments. In some instances, the excitation signal extracted byamplifier 204 is sent to the wireless transceiver 206 for wirelesstransmission to remote devices such as the computing device 180 shown inFIG. 4.

In the illustrated embodiment of FIG. 5, conductors 208 and 210 carrythe proximal pressure signal from the proximal pressure sensingcomponent 196 back to the proximal pressure input 197 of the hemodynamicsystem. In that regard, an amplifier 212 is electrically connected tothe conductors 208 and 210 as shown. The amplifier 212 is an operationalamplifier in some embodiments. The amplifier 212 is configured tomonitor or sample the proximal pressure signal (i.e., aortic pressuresignal) being supplied from the proximal pressure sensing component 196.The sampled proximal pressure signal is then sent to the wirelesstransceiver 206 for wireless transmission to remote devices such as thecomputing device 180 shown in FIG. 4. In some instances the sampledproximal pressure signal is converted from an analog signal to a digitalsignal prior to being provided to the wireless transceiver 206, but, inother instance, the wireless transceiver 206 performed theanalog-to-digital conversion itself. Accordingly, both the excitationsignal/voltage sampled from conductors 200 and 202 and the proximalpressure signal sampled from conductors 208 and 210 are fed to thewireless transceiver 206 for transmission. In this manner, an aorticpressure signal received from an aortic pressure sensing transducer maybe transmitted directly to a computing device where the aortic pressuresignal may be utilized in various calculations. The computing devicetherefore does not need to rely on receiving the aortic pressure signalfrom a hemodynamic system, which may provide unreliable data.

As noted above, the interface 170 is also configured to receive andprocess distal pressure signals from a distal pressure sensing component191. In that regard, in some instances, the wireless transceiver 206 isconfigured to associate the distal pressure signal with the proximalpressure and wireless transmit them together to a remote device wherepressure-based diagnostic characterizations may be calculated. In someinstances, a single distal pressure signal and a single proximalpressure signal are each represented by 2 bytes of data. With an examplesampling rate of 200 Hz, the wireless transceiver 206 may transmitapproximately 800 bytes per second—well within the data transmissionrate limits of most wireless communication standards. In other instance,the distal pressure signal and the proximal pressure signal may berepresented by different amounts of data and the sampling rate may bedifferent, requiring the wireless transceiver 206 to transmit a greateror smaller amount of data every second. And as described above, thewireless transceiver 206 may associate identifying information with thepressure signals, which would increase the amount of data wirelesslytransmitted.

In some instances, the interface 170 includes a microprocessor thatcalculates the proximal pressure based on the excitation signal voltage(Vexc), and the proximal pressure sensing component's output, and thecalculated values are provided to the wireless transceiver 206 fortransmission. In that regard, the proximal pressure sensing component'soutput conforms to the AAMI standard of 5 uV/Vexc/mmHg in someinstances. For an AC excitation signal, the microprocessor must measurethe proximal pressure signal voltage in synchrony with the excitationwaveform. In some instances, rather than the low-level inputs describedabove, the proximal pressure signal is received by the interface 170 asa high level signal. For example, the proximal pressure signal is a highlevel signal from a Volcano LoMap (available from Volcano Corporation)or from an external hemo system.

In some embodiments, the input/output connectors 194 and 195 are alsoused to facilitate energy harvesting from the hemo system or otherpressure measuring system. In that regard, to eliminate the need for anadditional power supply within the interface 170, the power extractioncircuit 220 may be connected to conductors 200 and 202 and utilized toextract a small amount of power from the hemo system's excitationvoltage for the proximal pressure sensing component 196 and convert itinto the power needed to run the remaining circuitry of the interface170, including the wireless transceiver 206. As noted above, whenconnected to the proximal pressure sensing side the power extractioncircuit 220 is still configured to extract power from the excitationsignal sent from the controller/computing device such that the extractedpower can be used to power the components of interface 170. Since theexcitation signal can be AC, positive or negative DC, and/or havevarious wave form shapes and voltages, the power extraction circuit 220must be able to accept these and convert to a regulated power supplywithout distorting the waveform that continues on to the proximalpressure sensing component 196. This is necessary to avoid affecting thepressure measurements obtained by the proximal pressure sensingcomponent 196. The voltage extracted from the excitation signal isconverted to a regulated Vcc voltage to operate the low power circuitryusing a buck or boost regulator depending on the input voltage.

In some instances, a signal conditioning portion 216 of the interface170 is in communication with input 190 that receives the distal pressuresignal. Referring now to FIG. 6, shown therein is a schematic of aportion the interface 170 according to an exemplary embodiment of thepresent disclosure. In particular, FIG. 6 shows a schematic of anexemplary embodiment of signal conditioning portion 216 of the interface170. In that regard, the signal condition portion 216 is configured tocondition signals received from the distal pressure measurement device.The signal conditioning portion 216 provides the excitation andamplification required for the distal pressure measurement device'spressure sensors, Ra and Rb, which collective form distal pressuresensing component 191 in some instances.

Calibration coefficients provided by the distal pressure measurementdevice utilizing an EPROM in the device connector, for example, are readto adjust the gain, offset, and temperature sensitivity for the device.The read values are used to adjust the three Digital to AnalogConverters (DACs) 224, 226, and 228, in the distal pressure front endcircuitry 216 that control the gain, offset, and temperature (TC)compensation, respectively. The distal pressure signal is then digitizedwith an Analog to Digital Converter 230, ADC, and sent to the wirelesstransceiver 206. The wireless transceiver 206 can then wirelesslytransmit the distal pressure to a remote device for furthercalculations. For example, a computing device that wirelessly receivesthe transmitted distal pressure and/or distal pressure waveform and theproximal pressure and/or proximal pressure waveform may use them tocalculate FFR, calculate iFR, calculate a pressure differential betweenthe proximal and distal pressures, identify a suitable diagnostic windowfor performing a pressure differential calculation without administeringa hyperemic agent to the patient, calculate a pressure differentialduring the identified diagnostic window, and/or combinations thereof.

Referring now to FIG. 7, shown therein is a schematic of a portion theinterface 170 according to another exemplary embodiment of the presentdisclosure. In particular, FIG. 7 shows a schematic of an exemplaryembodiment of signal conditioning portion 216′ of the interface 170. Inthat regard, the signal condition portion 216′ is configured tocondition signals received from the distal pressure measurement device.The signal conditioning portion 216′ provides the excitation andamplification required for the distal pressure measurement device'spressure sensors, Ra and Rb, which collective form distal pressuresensing component 191 in some instances. The distal pressure signal fromthe pressure sensors, Ra and Rb, is digitized with a two-channel Analogto Digital Converter 230, ADC, and sent to the wireless transceiver 206transmission. In the embodiments in which the interface 170 includes amicroprocessor, calibration coefficients provided by the distal pressuremeasurement device utilizing an EPROM 222 in the device connector, forexample, are read by the microprocessor to adjust the gain, offset,and/or temperature sensitivity for the device. The read values are usedby the microprocessor to control the gain, offset, and/or temperaturecompensation. Firmware within the microprocessor is utilized to controlthese parameters in some instances. The microprocessor can then utilizethe distal pressure or the distal pressure waveform for additionalcalculations. For example, in some instances the microprocessor utilizesthe distal pressure and/or distal pressure waveform with the proximalpressure and/or proximal pressure waveform to calculate FFR, calculate apressure differential between the proximal and distal pressures,identify a suitable diagnostic window for performing a pressuredifferential calculation without administering a hyperemic agent to thepatient, calculate a pressure differential during the identifieddiagnostic window, and/or combinations thereof. Any of thesecalculations may be provided to the wireless transceiver 206 forwireless transmission to one or more remote devices. Accordingly, thesignal conditioning portion 216′ of FIG. 7 provides similarfunctionality to the signal conditioning device 216 of FIG. 6, butwithout the need for the three Digital to Analog Converters (DACs) 224,226, and 228.

Referring again to FIG. 5, the interface 170 is also configured tooutput the distal pressure signal to an input 193 of a hemodynamicsystem. In that regard, the wireless transceiver 206 or a separatemicroprocessor within the interface 170 provides a digitized signal toan additional set of DACs in the distal output circuitry 218 thatmodulate the excitation of the hemo system to provide a proportionaldistal waveform of the distal pressure voltage back to the hemo systemthrough output 192. In some embodiments, the scaled voltage returned isthe same as a standard proximal pressure transducer, 5 uV/Vexc/mmHg, perthe AAMI standards. The output stage 218 modulates the externalexcitation of the hemo system to provide a duplicate wave shape, or a DCvoltage, scaled to 5 μV/Vexc/mmHg, per AAMI standards for aortictransducers of the distal pressure for the hemo system. Accordingly, byoutputting the distal pressure signal through output 192 and theproximal pressure signal through output 196, both proximal and distalpressures can then be observed on the hemo system's display using thehemo system's standard low-level inputs.

As noted above, in some instances in which the interface 170 includes amicroprocessor either integrated into or distinct from the wirelesstransceiver 206, the interface uses the proximal and distal pressuredata received from the instruments to calculate and display informationthat can be useful in the evaluation of the vessel and, in particular,evaluation of a stenosis of the vessel. In some instances, the interfaceis configured to calculate and display FFR. For an FFR measurement, themicroprocessor first normalizes the distal pressure to the aorticpressure. The distal and aortic pressures will become disparaging as thedistal pressure wire crosses the arterial lesion. The peak differencebetween the two pressures is captured automatically, or with a manualbutton press, and an FFR calculation started. The resultant number isshown on the display. The peak difference is typically measured duringhyperemia with the use of drugs like adenosine

In some embodiments the interface 170 includes external user-controlledbuttons. In one particular embodiment, one of the buttons causes themicroprocessor to ‘normalize’ the distal pressure measurement to theproximal pressure measurement. This is typically performed with thepressure sensing components 191 and 196 positioned in close proximity toone another within the patient such that they are subjected to similarpressures. In some instances, this calibration is performed proximal ofthe lesion and before the distal pressure sensing component 191 isadvanced distally beyond the lesion. After the distal pressure sensingcomponent 191 is placed beyond the suspect lesion actuation of anotherbutton causes the microprocessor to calculate the ratio of the distalpressure to the proximal pressure, which provides an FFR value orpressure differential. In that regard, in some implementations thebutton is pressed by a user at a precise moment during hyperemia basedon observation of the proximal and distal waveforms, which may bedisplayed on a separate device (e.g., a display of the hemo system) ordisplayed on a display of interface 170. Alternatively, thedetermination of the appropriate moment for the FFR calculation can bedone automatically by the microprocessor. In that regard, in someinstances the FFR calculation is performed at a point coinciding withthe peak difference between the distal and proximal (aortic) pressures.In some embodiments, a pressure differential is calculated during adiagnostic window without application of a hyperemic agent, as discussedbelow. In such embodiments, the pressure measurements and/or thepressure differential may be displayed continuously.

In that regard, in some instances the interface 170 is configured toprovide pressure measurements and/or pressure differentials based onevaluation techniques as described in one or more of UK PatentApplication Publication No. GB 2479340 A, filed Mar. 10, 2010 and titled“METHOD AND APPARATUS FOR THE MEASUREMENT OF A FLUID FLOW RESTRICTION INA VESSEL”, UK Patent Application No. GB 1100137.7, filed Jan. 6, 2011and titled “APPARATUS AND METHOD OF ASSESSING A NARROWING IN A FLUIDFILLED TUBE”, U.S. Provisional Patent Application No. 61/525,739, filedon Aug. 20, 2011 and titled “Devices, Systems and Methods for Assessinga Vessel,” and U.S. Provisional Patent Application No. 61/525,736, filedon Aug. 20, 2011 and titled “Devices, Systems, and Methods for VisuallyDepicting a Vessel and Evaluating Treatment Options,” each of which ishereby incorporated by reference in its entirety.

In some embodiments, the interface 170 is utilized to calculate anddisplay FFR in a traditional FFR procedure where the patient isadministered a hyperemic agent. In other embodiments, the interface 170is utilized to calculate a pressure differential similar to FFR (i.e.,the ratio of distal pressure to proximal pressure) but without the useof a hyperemic agent. In that regard, a suitable diagnostic window formaking such calculations must be determined and/or identified to have auseful measurement. The diagnostic window for evaluating differentialpressure across a stenosis without the use of a hyperemic agent inaccordance with the present disclosure may be identified based oncharacteristics and/or components of one or more of proximal pressuremeasurements, distal pressure measurements, proximal velocitymeasurements, distal velocity measurements, ECG waveforms, and/or otheridentifiable and/or measurable aspects of vessel performance. In thatregard, various signal processing and/or computational techniques can beapplied to the characteristics and/or components of one or more ofproximal pressure measurements, distal pressure measurements, proximalvelocity measurements, distal velocity measurements, ECG waveforms,and/or other identifiable and/or measurable aspects of vesselperformance to identify a suitable diagnostic window.

In some embodiments, the determination of the diagnostic window and/orthe calculation of the pressure differential are performed inapproximately real time or live to identify the diagnostic window andcalculate the pressure differential. In that regard, calculating thepressure differential in “real time” or “live” within the context of thepresent disclosure is understood to encompass calculations that occurwithin 10 seconds of data acquisition. It is recognized, however, thatoften “real time” or “live” calculations are performed within 1 secondof data acquisition. In some instances, the “real time” or “live”calculations are performed concurrent with data acquisition. In someinstances the calculations are performed by a processor in the delaysbetween data acquisitions. For example, if data is acquired from thepressure sensing devices for 1 ms every 5 ms, then in the 4 ms betweendata acquisitions the processor can perform the calculations. It isunderstood that these timings are for example only and that dataacquisition rates, processing times, and/or other parameters surroundingthe calculations will vary. In other embodiments, the pressuredifferential calculation is performed 10 or more seconds after dataacquisition. For example, in some embodiments, the data utilized toidentify the diagnostic window and/or calculate the pressuredifferential are stored for later analysis.

In some instances, the diagnostic window is selected by identifying aportion of the cardiac cycle corresponding to a time period in which thechange in velocity (i.e., dU) fluctuates around zero. Time periods wherethe change in velocity is relatively constant and approximately zero(i.e., the speed of the fluid flow is stabilized) are suitablediagnostic windows for evaluating a pressure differential across astenosis of a vessel without the use of a hyperemic agent in accordancewith the present disclosure. In that regard, in a fluid flow system, theseparated forward and backward generated pressures are defined by:

${d\; P_{+}} = {\frac{1}{2}( {{d\; P} + {\rho\; c\; d\; U}} )}$and${{d\; P_{-}} = {\frac{1}{2}( {{d\; P} - {\rho\; c\; d\; U}} )}},$

where dP is the differential of pressure, p is the density of the fluidwithin the vessel, c is the wave speed, and dU is the differential offlow velocity. However, where the flow velocity of the fluid issubstantially constant, dU is approximately zero and the separatedforward and backward generated pressures are defined by:

${d\; P_{+}} = {{\frac{1}{2}( {{d\; P} + {\rho\;{c(0)}}} )} = {\frac{1}{2}d\; P}}$and${d\; P_{-}} = {{\frac{1}{2}( {{d\; P} - {\rho\;{c(0)}}} )} = {\frac{1}{2}d\;{P.}}}$

In other words, during the time periods where dU is approximately zero,the forward and backward generated pressures are defined solely bychanges in pressure.

Accordingly, during such time periods the severity of a stenosis withinthe vessel can be evaluated based on pressure measurements takenproximal and distal of the stenosis. In that regard, by comparing theforward and/or backward generated pressure distal of a stenosis to theforward and/or backward generated pressure proximal of the stenosis, anevaluation of the severity of the stenosis can be made. For example, theforward-generated pressure differential can be calculated as

$\frac{d\; P_{+ {distal}}}{d\; P_{+ {proximal}}},$while the backward-generated pressure differential can be calculated as

$\frac{d\; P_{- {distal}}}{d\; P_{- {proximal}}}.$

In the context of the coronary arteries, a forward-generated pressuredifferential is utilized to evaluate a stenosis in some instances. Inthat regard, the forward-generated pressure differential is calculatedbased on proximally originating (i.e., originating from the aorta)separated forward pressure waves and/or reflections of the proximallyoriginating separated forward pressure waves from vascular structuresdistal of the aorta in some instances. In other instances, abackward-generated pressure differential is utilized in the context ofthe coronary arteries to evaluate a stenosis. In that regard, thebackward-generated pressure differential is calculated based on distallyoriginating (i.e., originating from the microvasculature) separatedbackward pressure waves and/or reflections of the distally originatingseparated backward pressure waves from vascular structures proximal ofthe microvasculature.

In yet other instances, a pressure wave is introduced into the vessel byan instrument or medical device. In that regard, the instrument ormedical device is utilized to generate a proximally originating forwardpressure wave, a distally originating backward pressure wave, and/orcombinations thereof for use in evaluating the severity of the stenosis.For example, in some embodiments an instrument having a movable membraneis positioned within the vessel. The movable membrane of the instrumentis then activated to cause movement of the membrane and generation of acorresponding pressure wave within the fluid of the vessel. Based on theconfiguration of the instrument, position of the membrane within thevessel, and/or the orientation of the membrane within the vessel thegenerated pressure wave(s) will be directed distally, proximally, and/orboth. Pressure measurements based on the generated pressure wave(s) canthen be analyzed to determine the severity of the stenosis.

There are a variety of signal processing techniques that can be utilizedto identify time periods where the change in velocity is relativelyconstant and approximately zero, including using a differential, firstderivative, second derivative, and/or third derivative of the velocitymeasurement are utilized. For example, identifying time periods duringthe cardiac cycle where the first derivative of velocity is relativelyconstant and approximately zero allows the localization of time periodswhere velocity is relatively constant. Further, identifying time periodsduring the cardiac cycle where the second derivative of velocity isrelatively constant and approximately zero allows the localization of atime period where acceleration is relatively constant and near zero, butnot necessarily zero.

While examples of specific techniques for selecting a suitablediagnostic window have been described above, it is understood that theseare exemplary and that other techniques may be utilized. In that regard,it is understood that the diagnostic window is determined using one ormore techniques selected from: identifying a feature of a waveform orother data feature and selecting a starting point relative to theidentified feature (e.g., before, after, or simultaneous with thefeature); identifying a feature of a waveform or other data feature andselecting an ending point relative to the identified feature (e.g.,before, after, or simultaneous with the feature); identifying a featureof a waveform or other data feature and selecting a starting point andan ending point relative to the identified feature; identifying astarting point and identifying an ending point based on the startingpoint; and identifying an ending point and indentifying a starting pointbased on the ending point. Additional details of techniques forselecting a suitable diagnostic window are described in U.S. ProvisionalPatent Application No. 61/525,739, filed on Aug. 20, 2011 and titled“Devices, Systems and Methods for Assessing a Vessel,” which is herebyincorporated by reference in its entirety. In that regard, it isunderstood that the interface 170 may be programmed to determine one ormore diagnostic windows based on the techniques described in the presentdisclosure, including those incorporated by reference, and/or includeone or more hardware features configured to identify one or morediagnostic windows based on the techniques described in the presentdisclosure, including those incorporated by reference.

Further, for a variety of reasons the proximal pressure measurements andthe distal pressure measurements received by the interface 170 are nottemporally aligned in some instances. For example, during dataacquisition, there will often be a delay between the distal pressuremeasurement signals and the proximal pressure measurement signals due tohardware signal handling differences between the instrument(s) utilizedto obtain the measurements. In that regard, the differences can comefrom physical sources (such as cable length and/or varying electronics)and/or can be due to signal processing differences (such as filteringtechniques). The resulting delay between the signals is between about 5ms and about 150 ms in some instances. Because individual cardiac cyclesmay last between about 500 ms and about 1000 ms and the diagnosticwindow may be a small percentage of the total length of the cardiaccycle, longer delays between the proximal and distal pressuremeasurement signals can have a significant impact on alignment of thepressure data for calculating a pressure differential for a desireddiastolic window of a cardiac cycle.

As a result, in some instances, it is necessary to shift one of theproximal and distal pressures relative to the other of the distal andproximal pressures in order to temporally align the pressuremeasurements. For example, a portion of the distal pressure measurementor proximal pressure measurement may be shifted to be temporally alignedwith a corresponding portion of the proximal pressure measurement ordistal pressure measurement, respectively, coinciding with thediagnostic window. While a shift of only a portion of the distal orproximal pressure measurement associated with the diagnostic window isutilized in some instances, in other instances all or substantially allof the proximal and distal pressures are aligned before the portionscorresponding to a selected diagnostic window are identified.

Alignment of all or portion(s) of the proximal and distal pressures isaccomplished using a hardware approach in some instances. For example,one or more hardware components are positioned within the communicationpath of the proximal pressure measurement, the distal pressuremeasurement, and/or both to provide any necessary delays to temporallyalign the received pressure signals. In some instances, these hardwarecomponents are positioned within the interface 170. In other instances,alignment of all or portion(s) of the proximal and distal pressures isaccomplished using a software approach. For example, a cross-correlationfunction or matching technique is utilized to align the cardiac cyclesin some embodiments. In other embodiments, the alignment is based on aparticular identifiable feature of the cardiac cycle, such as an ECGR-wave or a pressure peak. Additionally, in some embodiments alignmentis performed by a software user where adjustments are made to the delaytime of at least one of the proximal and distal pressures until thecardiac cycles are visually aligned to the user. A further technique foraligning the signals is to apply a synchronized timestamp at the pointof signal acquisition. Further, in some instances combinations of one ormore of hardware, software, user, and/or time-stamping approaches areutilized to align the signals.

Regardless of the manner of implementation, several approaches areavailable for the aligning the proximal and distal pressure measurementsignals. In some instances, each individual distal pressure measurementcardiac cycle is individually shifted to match the correspondingproximal pressure measurement cardiac cycle. In other instances, anaverage shift for a particular procedure is calculated at the beginningof the procedure and all subsequent cardiac cycles during the procedureare shifted by that amount. This technique requires little processingpower for implementation after the initial shift is determined, but canstill provide a relatively accurate alignment of the signals over thecourse of a procedure because the majority of the signal delay is due tofixed sources that do not change from patient to patient or within theprocedure. In yet other instances, a new average shift is calculatedeach time that the proximal and distal pressure signals are normalizedto one another during a procedure. In that regard, one or more timesduring a procedure the sensing element utilized for monitoring pressuredistal of the stenosis is positioned adjacent the sensing elementutilized for monitoring pressure proximal of the stenosis such that bothsensing elements should have the same pressure reading. If there is adifference between the pressure readings, then the proximal and distalpressure signals are normalized to one another. As a result, thesubsequently obtained proximal and distal pressure measurements are moreconsistent with each other and, therefore, the resulting pressuredifferential calculations are more accurate.

With the proximal and distal pressure measurements aligned, the pressuredifferential for the diagnostic window is calculated. In some instances,the pressure differential is calculated using average values for theproximal and distal pressure measurements across the diagnostic window.The pressure differential calculations of the present disclosure areperformed for a single cardiac cycle, in some instances. In otherinstances, the pressure differential calculations are performed formultiple cardiac cycles. In that regard, accuracy of the pressuredifferential can be improved by performing the pressure differentialcalculations over multiple cardiac cycles and averaging the valuesand/or using an analysis technique to identify one or more of thecalculated values that is believed to be most and/or least accurate.

One advantage of the techniques of the present disclosure foridentifying diagnostic windows and evaluating pressure differentials isthe concept of “beat matching”. In that regard, the proximal and distalwaveforms for the same cardiac cycle are analyzed together with noaveraging or individual calculations that span more than a singlecardiac cycle. As a result, interruptions in the cardiac cycle (such asectopic heartbeats) equally affect the proximal and distal recordings.As a result, these interruptions that can be detrimental to current FFRtechniques have minor effect on the techniques of the presentdisclosure. Further, in some embodiments of the present disclosure, theeffect of interruptions in the cardiac cycle and/or other irregularitiesin the data is further minimized and/or mitigated by monitoring thepressure differential calculations to detect these anomalies andautomatically exclude the impacted cardiac cycles.

In one particular embodiment, pressure differential is calculated on twosequential cardiac cycles and the individual pressure differentialvalues are averaged. The pressure differential of a third cycle is thencalculated. The average value of the pressure differentials is comparedto the average pressure differential using three cycles. If thedifference between the averages is below a predetermined thresholdvalue, then the calculated value is considered to be stable and nofurther calculations are performed. For example, if a threshold value of0.001 is used and adding an additional cardiac cycle changes the averagepressure differential value by less than 0.001, then the calculation iscomplete. However, if the difference between the averages is above thepredetermined threshold value, then the pressure differential for afourth cycle is calculated and a comparison to the threshold value isperformed. This process is repeated iteratively until the differencebetween the averages of cardiac cycle N and cardiac cycle N+1 is belowthe predetermined threshold value. As the pressure differential value istypically expressed to two decimal places of precision (such as 0.80),the threshold value for completing the analysis is typically selected tobe small enough that adding a subsequent cardiac cycle will not changethe pressure differential value. For example, in some instances thethreshold value is selected to be between about 0.0001 and about 0.05.

In some instances, the level of confidence calculation has differentthresholds depending on the degree of stenosis and/or an initialcalculated pressure differential value. In that regard, pressuredifferential analysis of a stenosis is typically based around a cutoffvalue(s) for making decisions as to what type of therapy, if any, toadminister. Accordingly, in some instances, it is desirable to be moreaccurate around these cutoff points. In other words, where thecalculated pressure differential values are close to a cut-off, a higherdegree of confidence is required. For example, if the cutoff for atreatment decision is at 0.80 and the initial calculated pressuredifferential measurement is between about 0.75 and about 0.85, then ahigher degree of confidence is needed than if the initial calculatedpressure differential measurement is 0.40, which is far from the 0.80cutoff point. Accordingly, in some instances the threshold value is atleast partially determined by the initial calculated pressuredifferential measurement. In some instances, the level of confidence orstability of the calculated pressure differential is visually indicatedto user via a software interface.

Because pressure differential can be calculated based on a singlecardiac cycle in accordance with the present disclosure, a real-time orlive pressure differential calculation can made while the distalpressure measuring device is moved through the vessel. Accordingly, insome instances the system includes at least two modes: asingle-cardiac-cycle mode that facilitates pressure differentialcalculations while moving the distal pressure measuring device throughthe vessel and a multi-cardiac-cycle mode that provides a more precisepressure differential calculation at a discrete location. In oneembodiment of such a system, the interface 170 is configured to providethe live pressure differential value until the distal pressure measuringdevice is moved to the desired location and a measurement button isselected and/or some other actuation step is taken to trigger themulti-cardiac-cycle mode calculation.

Persons skilled in the art will also recognize that the apparatus,systems, and methods described above can be modified in various ways.Accordingly, persons of ordinary skill in the art will appreciate thatthe embodiments encompassed by the present disclosure are not limited tothe particular exemplary embodiments described above. In that regard,although illustrative embodiments have been shown and described, a widerange of modification, change, and substitution is contemplated in theforegoing disclosure. It is understood that such variations may be madeto the foregoing without departing from the scope of the presentdisclosure. Accordingly, it is appropriate that the appended claims beconstrued broadly and in a manner consistent with the presentdisclosure.

What is claimed is:
 1. An interface for intravascular pressure sensingdevices, comprising: a distal input connector configured to receive adistal pressure signal from a distal pressure sensing device; a distaloutput connector configured to output the distal pressure signaldirectly to a hemodynamic system in a format useable by the hemodynamicsystem; a proximal input connector configured to receive a proximalpressure signal from a proximal pressure sensing device; a proximaloutput connector configured to output the proximal pressure signaldirectly to the hemodynamic system in a format useable by thehemodynamic system, wherein the distal input connector, the distaloutput connector, the proximal input connector, and the proximal outputconnector are coupled to a single housing; a first amplifier; and asingle wireless transceiver coupled to the single housing, wherein theproximal pressure sensing device communicates with the hemodynamicsystem via at least two leads, wherein the at least two leads extendfrom the proximal input connector to the proximal output connectorwithin the single housing, wherein the at least two leads are associatedwith sending an excitation signal from the hemodynamic system to theproximal pressure sensing device, wherein the first amplifier iselectrically coupled with the at least two leads, the first amplifierconfigured to sample the excitation signal while the excitation signalis sent to the proximal pressure sensing device, and wherein the singlewireless transceiver is configured to wirelessly transmit the excitationsignal, the distal pressure signal, and the proximal pressure signal toa computing system spaced from the interface, wherein the computingsystem is distinct from the hemodynamic system.
 2. The interface ofclaim 1, wherein the single housing has a width between 5 cm and 25 cm,a height between 5 cm and 25 cm, and a depth between 1 cm and 10 cm. 3.The interface of claim 2, wherein the distal pressure sensing device isa pressure-sensing guidewire.
 4. The interface of claim 3, wherein theproximal pressure sensing device is a pressure-sensing catheterconfigured for use with the hemodynamic system.
 5. The interface ofclaim 4, wherein the pressure-sensing catheter communicates with thehemodynamic system via at least four leads.
 6. The interface of claim 5,wherein a second pair of leads of the at least four leads are associatedwith sending the proximal pressure signal from the proximal pressuresensing device to the hemodynamic system.
 7. The interface of claim 6,further comprising a second amplifier electrically coupled with the pairof leads, the second amplifier configured to sample the proximalpressure signal.
 8. The interface of claim 7, wherein the secondamplifier sends the sampled proximal pressure signal to the singlewireless transceiver.
 9. The interface of claim 1, wherein the firstamplifier sends the sampled excitation signal to the single wirelesstransceiver.
 10. The interface of claim 1, further comprising a powerextraction device coupled to the at least two leads that receive theexcitation signal from the hemodynamic system, the power extractiondevice being configured to extract power from the excitation signal foruse in operating at least the single wireless transceiver, wherein theat least two leads are associated with a proximal pressure measurementinput of the hemodynamic system.
 11. The interface of claim 1, furthercomprising a power extraction device coupled to a pair of leads thatreceive a further excitation signal from the hemodynamic system, thepower extraction device being configured to extract power from thefurther excitation signal for use in operating at least the singlewireless transceiver, wherein the pair of leads is associated with adistal pressure measurement input connector of the hemodynamic system.12. The interface of claim 1, wherein the single wireless transceiver isfurther configured to wirelessly transmit identifying patientinformation with the distal pressure and the proximal pressure to thecomputing system.
 13. The interface of claim 1, wherein the distal inputconnector is configured to receive a distal pressure signal directlyfrom a distal pressure sensing device connector, and wherein theproximal input connector is configured to receive a proximal pressuresignal directly from a proximal pressure sensing device connector. 14.The interface of claim 1, wherein the single wireless transceiver isconfigured to wirelessly transmit the distal pressure signal and theproximal pressure signal to the computing system via a secure,compressed, or encrypted link.
 15. A system for evaluating a vascularstenosis, the system comprising: a distal pressure sensing device sizedand shaped for insertion into human vasculature; and an interfaceconfigured to receive input from the distal pressure sensing device anda proximal pressure sensing device, and provide output to a computingsystem and directly to a hemodynamic system, the interface comprising: adistal input connector configured to receive a distal pressure signalfrom the distal pressure sensing device; a proximal input connectorconfigured to receive a proximal pressure signal from the proximalpressure sensing device; a proximal output connector configured tooutput the proximal pressure signal to the hemodynamic system in aformat useable by the hemodynamic system; a distal output connectorconfigured to output the distal pressure signal to the hemodynamicsystem in a format useable by the hemodynamic system, wherein the distalinput connector, the distal output connector, the proximal inputconnector, and the proximal output connector are coupled to a singlehousing; a first amplifier; and a single wireless transceiver coupled tothe single housing, wherein the proximal pressure sensing devicecommunicates with the hemodynamic system via at least two leads, whereinthe at least two leads extend from the proximal input connector to theproximal output connector within the single housing, wherein the atleast two leads are associated with sending an excitation signal fromthe hemodynamic system to the proximal pressure sensing device, whereinthe first amplifier is electrically coupled with the at least two leads,the first amplifier configured to sample the excitation signal while theexcitation signal is sent to the proximal pressure sensing device, andwherein the single wireless transceiver is configured to wirelesslytransmit the excitation signal, the distal pressure signal, and theproximal pressure signal to the computing system, wherein the computingsystem is spaced from and distinct from the hemodynamic system.
 16. Thesystem of claim 15, wherein the single wireless transceiver isconfigured to wirelessly transmit the distal pressure and the proximalpressure using one of IEEE 802.11 standards and IEEE 802.15 standards.17. The system of claim 15, wherein the interface further includes aprocessor coupled to the distal input, distal output, proximal input,and proximal output, the processor configured to calculate a pressuredifferential between a distal pressure based on the received distalpressure signal and a proximal pressure based on the excitation signaland the received proximal pressure signal; and wherein the wirelesstransceiver is further configured to wirelessly transmit the pressuredifferential to the computing system spaced from the interface.
 18. Thesystem of claim 15, wherein a first electrical path extends within thesingle housing between the wireless transceiver and the distal inputconnector, wherein at least four leads extend between the proximalpressure sensing device to the hemodynamic system, wherein the at leastfour leads include the at least two least two leads extending from theproximal input connector to the proximal output connector within thesingle housing, wherein signals of a second electrical path and a thirdelectrical path are transmitted along at least a portion of the at leastfour leads, and wherein the third electrical path extends between thewireless transceiver and the proximal input connector, wherein the thirdelectrical path includes a second amplifier configured to sample theproximal pressure signal transmitted along the second electrical pathand transmit the proximal pressure signal to the single wirelesstransceiver.
 19. The system of claim 15, wherein the single wirelesstransceiver is configured to receive power from the hemodynamic systemvia the distal output connector or proximal output connector.
 20. Thesystem of claim 15, wherein communicative connections between theinterface and the hemodynamic system are wired, and a communicativeconnection between the interface and the computing system is wireless.